Chronic Traumatic Encephalopathy Limiting Sports Helmet

ABSTRACT

A smart hard shell helmet for protection of head injury having a plurality of air filled inflatable bladders inside the shell, a valve on at least one bladder that responds to a controller, at least one flexible extendible strap extended from the bladder to a one point on the inside of the helmet, accelerometers operably connected to the helmet and wearer&#39;s head for sensing g force changes, pressure sensors in the bladders, an electrically actuated valve responsive to pressure and force measurement determined by the controller thresholds being met, and the valve exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder.

CROSS REFERENCE TO RELATED APPLICATIONS

Not Applicable.

BACKGROUND OF THE INVENTION

The present invention relates to helmets, and more particularly to a sports helmet that utilizes microprocessor controlled valves and re-inflatable bladders for reducing head impact in the helmet and configured for customizable operation.

The present invention is an improvement in headgear or helmets for high impact sports such as football, lacrosse, or any other sport where potential head injury can occur. Previous attempts at reducing such injuries have resulted in helmets with more internal cushioning, advanced materials, or design of the shell to withstand impact. These solutions fail to significantly diminish the G forces that are repeatedly experienced by football players during practice and games, which are the leading cause of chronic traumatic encephalopathy in athletes. Further, prior attempts to create injury reducing helmets were not configurable for a particular user, or useable repeatedly during play.

BRIEF SUMMARY OF THE INVENTION

A primary advantage of the invention is to provide a helmet and method of reducing head injury in high impact sports.

Another advantage of the invention is to provide a customizable helmet that operates based on collected data for a particular user.

Yet another advantage of the invention is to provide a helmet with re-inflatable bladders to cushion head impact within the helmet.

Still yet another advantage of the invention is to provide a software collection system of impacts to permit fine-tuning of the bladder, valve and microprocessor control of the helmet.

Yet another advantage of the invention is to provide an immediate resettable helmet system that can be used over and over during play.

In accordance with a preferred embodiment of the present invention, there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, the bladders on the interior surface of the shell, a valve disposed on at least one bladder responsive to signals from a controller, at least one flexible extendible strap having a first relaxed state and a second extended state operably engaged to at least one bladder and at least one point on the inside of the helmet, at least one accelerometer attached to the helmet operably connected to the helmet body for sensing g force change on the helmet in operation, at least a second accelerometer operably connected to the wearer's head for sensing g force change on the wearer's head in operation, an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met, and the valve, in response to control signals from a controller, exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder.

In accordance with another embodiment of the invention, there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, the bladders on the interior surface of the shell, a valve disposed on at least one bladder responsive to signals from a controller, at least one flexible extendible strap having a first relaxed state and a second extended state operably engaged to at least one bladder and at least one point on the inside of the helmet, at least one accelerometer attached to the helmet operably connected to the helmet body for sensing g force change on the helmet in operation, at least a second accelerometer operably connected to the wearer's head for sensing g force change on the wearer's head in operation, an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met, and the valve, in response to control signals from a controller, exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder.

In accordance with another preferred embodiment of the invention there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, each bladder positioned on the interior surface of the shell, a valve disposed on each bladder responsive to signals from a controller, a memory containing material in at least one bladder that re-inflates the bladder after an impact event by drawing atmospheric air through the valve, a least one accelerometer attached to the helmet operably connected to the helmet body for sensing acceleration change on the helmet in operation, at least a second accelerometer operably connected to the wearer's head for sensing g force change on the wearer's head in operation, an electrically actuated valve on the bladder responsive to an accelerometer measurement determined by the controller threshold being met; and where the controller produces a signal and the controller activates a motor by electrical power to one or more valves to an open state to expel air, and turns off electrical power to return the valves to a closed state.

Other objects and advantages will become apparent from the following descriptions, taken in connection with the accompanying drawings, wherein, by way of illustration and example, preferred embodiments of the present invention are disclosed.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side schematic view of a helmet having an internal air cushion bladder(s) according to a preferred embodiment of the invention.

FIG. 2 is a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 100 psig.

FIG. 3 is a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 120 psig.

FIG. 4 is a graph showing Acceleration vs. Head Displacement in Helmet with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with no pressure relief valve.

FIG. 5A is graph showing Acceleration vs. Head Displacement in Helmet for a 1 inch bladder height in a helmet with y axis from 0 to 300 g forces.

FIG. 5B is graph showing Acceleration vs. Head Displacement in Helmet for a 2 inch bladder height in a helmet with y axis from 0 to 100 g forces.

FIG. 5C is graph showing Acceleration vs. Head Displacement in Helmet for a 4 inch bladder height in a helmet with y axis from 0 to 100 g forces.

FIG. 6 is a graph showing Maximum Acceleration vs. Helmet Size in inches for an initial velocity of 13 ft/sec.

FIG. 7 is a graph showing Maximum Acceleration vs. Initial Velocity for a 4 inch bladder height.

FIG. 8 is a graph showing Maximum Acceleration vs. Initial Velocity for different typical NFL players and their speed before impact.

FIG. 9 is a side schematic of a helmet with microcontroller, accelerometers, and air cushioned bladders according to a preferred embodiment of the invention.

FIG. 10 is a schematic showing a cylindrical valve activated by an electric motor for releasing air pressure according to a preferred embodiment of the invention.

FIG. 11 is a flow chart of the operation of the helmet according to a preferred embodiment of the invention.

FIG. 12 is a block diagram of the main components of the helmet system according to a preferred embodiment of the invention.

FIG. 13 is a side schematic view of a helmet with bladder and straps in a contracted state according to a preferred embodiment of the invention.

FIG. 14 is a side schematic view of a helmet with bladder and straps in an extended state according to a preferred embodiment of the invention.

FIGS. 15A and 15B are side schematic views of a helmet with bladder and straps in a contracted and extended state according to a preferred embodiment of the invention.

FIG. 16 is a flow chart of customized and optimized size and bladder design for a helmet according to a preferred embodiment of the invention.

FIG. 17 is a flow chart of customized and optimized post hit processing software or firmware with annual updating for a helmet according to a preferred embodiment of the invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Detailed descriptions of the preferred embodiments are provided herein. It is to be understood, however, that the present invention may be embodied in various forms. Various aspects of the invention may be inverted, or changed in reference to specific part shape and detail, part location, or part composition. Therefore, specific details disclosed herein are not to be interpreted as limiting, but rather as a basis for the claims and as a representative basis for teaching one skilled in the art to employ the present invention in virtually any appropriately detailed system, structure or manner.

The drawings constitute a part of this specification and include exemplary embodiments to the invention, which may be embodied in various forms. It is to be understood that in some instances various aspects of the invention may be shown exaggerated or enlarged to facilitate an understanding of the invention.

Preferred embodiments of the present invention involve a number of innovations and use of microprocessor control to create an active, smart helmet configurable to an individual's physical dimensions, as well as their response to repeated head impacts through data collection by the helmet.

The impact on a player's head in a helmet with an air bladder cushion is generally shown by the following basic physics:

With initial velocity of player, when helmet is stopped, the player's head moves inside the helmet compressing the cushion material. The cushion exerts a decelerating force on the head according to the compression of the cushion, F=ma.

As the cushion material compresses, the force on the player's head increases as shown F=f(x). Deceleration increases as cushion is compressed a=f (x)/m. For fixed mass and spring constant, g's increase linearly with head displacement for most cushioning materials.

It has been observed that the following occurs with respect to helmet impacts: The higher the initial velocity for a given helmet height, the higher the max g's experienced; larger helmets limit max g's experienced; clamping the max pressure limits max g's but also extends head travel; to globally limit the max g's experienced, the clamping pressure must be adjusted for each head mass and initial velocity/helmet deceleration; and using the smart helmet concept to limit pressure according to initial velocity significantly reduces g forces experienced by a player.

According to a preferred embodiment of the invention, a helmet is provided that utilizes a multi-valved bladder under microprocessor control that opens one or more of the valves upon a certain level of g force impact or other displacement as sensed by on-board accelerometers. One or more bladders are operably connected to one or more valves that instantly open upon a signal from the microprocessor to relieve the bladder pressure and slow down head displacement in a safer and more controlled manner. The bladder may be made of a material that re-inflates itself due to internal structure or other means such as a small fan or motor controlled by the microprocessor or by straps that apply negative bias against the bladder so as to re-inflate after activation. The helmet would also be configured to accommodate the locations of different bladders of various shapes located in areas of most concern and the helmet may take on a more oval shape with higher central crown from top to bottom of the helmet. Data of previous impacts may be recorded and can be used to activate the bladder upon different impact profiles as determined by the processor.

Turning now to FIG. 1 there is shown a side schematic view of helmet 100 with hard shell 105 having in internal generally compressible bladder 110 with height 115 in an initial state. User has head 125 placed in contact with bladder 110 which upon impact has displacement direction 120. As will be more fully described below, bladder 110 cushions head 125 in displacement direction 120 to decelerate head 125. Bladder 110 may preferably be filled with open celled foam, or memory foam or have chambers that are filled with gas, air, or other fluid.

Turning now to FIG. 2 there is shown a graph 200 showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 100 psig. Line 215 shows displacement in inches versus pressure in pounds per square inch for a bladder height of 1 inch. Line 220 shows displacement 210 in inches versus pressure 205 in pounds per square inch for a bladder height of 2 inches. Line 225 shows displacement in inches versus pressure in pounds per square inch for a bladder height of 4 inches.

Turning now to FIG. 3 there is shown a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 120 psig. Pressure 305 is graphed against displacement 310 for the different bladder heights, with line 315 showing bladder height 1 inch, line 320 showing bladder height 2 inches, and line 325 showing bladder height 4 inches. Displacement 310 in inches shows the movement of a user's head and related pressure in pounds per square inch for each bladder height.

Turning now to FIG. 4 there is shown graph 400 showing Acceleration 405 vs. Head Displacement 410 with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with no pressure relief valve. Line 415 depicts the curve for a 1 inch bladder, line 420 depicts a curve for a 2 inch bladder, and line 425 depicts a curve for a 4 inch bladder.

Turning now to FIG. 5A there is shown graph 500 showing Acceleration vs. Head Displacement for a 1 inch bladder height in a helmet with y axis 505 from 0 to 300 g forces. X axis 510 is head displacement in inches. Line 515 shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line 520 shows acceleration with a maximum pressure relief of 22.8 psig with line 525 the point of maximum allowable displacement of 1 inch due to the bladder size. This demonstrates that with a 1 inch bladder, and a 13 feet/sec initial velocity, g forces of 57 g's are possible where line 525 crosses line 520. Line 535 shows that with pressure relief at 4.5 psig, a maximum acceleration of 11 g's would be possible, except that the head is traveling further than the bladder height, so this is not possible.

Turning now to FIG. 5B there is shown a graph 550 showing Acceleration vs. Head Displacement for a 2 inch bladder height in a helmet with y axis 555 from 0 to 100 g forces. X axis 560 is head displacement in inches. Line 570 shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line 580 shows acceleration with a maximum pressure relief of 18 psig with line 585 intersecting at displacement of 2 inches the point of maximum allowable displacement due to the bladder size. This demonstrates that with a 2 inch bladder, and a 13 feet/sec initial velocity, g forces of 20 g's are possible where line 585 crosses line 595, the maximum possible displacement due to the bladder height of 2 inches.

Turning now to FIG. 5C there is shown graph 551 showing Acceleration vs. Head Displacement for a 4 inch bladder height in a helmet with y axis 556 from 0 to 100 g forces. X axis 561 is head displacement in inches. Line 571 shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line 591 shows acceleration with a maximum pressure relief of 4 psig with line 591 intersecting at bladder height line 596 after allowable displacement due to the larger bladder size of 4 inches. This demonstrates that with a 4 inch bladder, and a 13 feet/sec initial velocity, g forces are limited to 10 g's and are contained.

Turning now to FIG. 6 there is shown a graph 600 showing Maximum Acceleration on y axis 605 vs. Helmet Size in inches on x axis 610 for an initial velocity of 13 ft/sec. Line 615 shows as helmet bladder size 610 increases, maximum acceleration from an initial velocity of 13 ft/sec 605 decreases.

Turning now to FIG. 7 there is shown a graph 700 showing Maximum Acceleration on y axis 705 vs. Initial Velocity on x axis 710 for a 4″ bladder height. Line 715 shows that as initial velocity 710 increases, with a 4 inch bladder height, head acceleration 705 increases.

Turning now to FIG. 8 there is shown graph 800 with Maximum Acceleration on y axis 805 vs. Initial Velocity on x axis 810 for different typical NFL players and their speed before impact represented by lines 820, 825, 830 and 835. Line 840 shows increasing head acceleration as initial velocity increases with a 4 inch bladder, and as the faster players shown in line 835 are involved in an impact, they do not exceed the concussion threshold line 815 since the maximum head acceleration line 840 crosses line 835 well below line 815, the concussion threshold. The higher the initial velocity 810, the higher the maximum g forces 805 are experienced for a given helmet height. However, these g forces are well below what would be experienced in the absence of the present invention. Line 845 shows an average game acceleration over multiple impacts.

Turning now to FIG. 9 is a side schematic of helmet 900 having an outer shell 105 with microcontroller 935, helmet shell 105 and head 125, accelerometers 925 and 930, respectively and air-cushioned bladder 905 according to a preferred embodiment of the invention. Accelerometer 925 is preferably operably attached to helmet shell 105 and accelerometer 930 is preferably operably connected to head 125, preferably via head cap 1310 as shown in FIGS. 13 and 14. Bladder 905 is shown with bladder height 950 which reduces acceleration of impacts as the size increases. Upon impact, bladder 905 receives force from the user's head 125 as it moves toward shell 105 causing microcontroller 935 upon receiving acceleration and pressure signals from accelerometers 925 and 930 and pressure sensors 936 disposed in bladder 905, signals to motor 1030 (FIG. 10) that electrically powers valves 940 to open and permit air to expel from bladder 905 when certain threshold pressure and/or acceleration limits are reached. Pressure sensors 936 are operably connected to microcontroller 935 that receives pressure readings. Once the impact event has ended as determined by the accelerometers and pressure sensors signaling to the microcontroller, valves 940 permit air to flow back into the bladder and re-inflate as further described below. The microcontroller or other storage device may transmit via Bluetooth® or other wireless protocol all acceleration and bladder pressure data totals to a storage device on the sidelines.

Turning now to FIG. 10 is a schematic showing cylindrical valve 1000 activated by electric motor 1030 that receives current from the microcontroller and from the battery, thereby alternating the magnetic field in windings 1050 through lines 1060 and 1065. As the electric current is applied to the winding 1050 of motor 1030, attached to the valve 1000, the valve rotates aligning the core 1005 with opening 1010 on the valve to permit airflow 1015 through valve 1000. When the current is turned off, the helical spring 1020 returns the valve to its closed position.

Turning now to FIG. 11 is a flow chart of the operation of the helmet according to a preferred embodiment of the invention. The flow begins with football hit 1105 that is sensed by helmet accelerometers that read the magnitude and direction of the helmet and head deceleration in box 1110. Box 1115 shows the microcontroller computing the optimum pressure to minimize head acceleration within the helmet envelop. Box 1120 shows where the head accelerometer begins logging magnitude and direction of player's head acceleration, and in box 1125 pressure sensors in each segment of the helmet bladder begin logging pressure data. Box 1113 shows that when pressure reaches an optimum limit, the microcontroller begins to open the valves to maintain no more than a maximum pressure. Box 1135 the head accelerometer logs the magnitude and direction of head g forces and modulates which valves to open or close accordingly. Box 1140 shows when the head accelerometer shows head g forces below a pre-determined threshold, the valves remain open all the way to re-inflate the bladder with elastic bands or other mechanism in the helmet and the process ends at block 1145.

Turning now to FIG. 12 is a block diagram 1200 of the main components of the helmet system according to a preferred embodiment of the invention. Block 1205 is individual player customized and optimized software and firmware with the potential for annual or other time period updating. Software controls microcontroller 1215 which in turn is operably connected to valves 1242, 1244, 1246 and 1248. Microcontroller 1215 is also operably connected to bladder compartments 1232, 1234, and 1236 through valves previously described. Helmet accelerometer 1210 and head accelerometer 1220 are also operably connected to microcontroller 1215.

Turning now to FIG. 13 is a side schematic view of helmet 1300 with hard shell 105 and attachment 1305 connecting the bladder to an elastic strap 1315 on one side and attached to the helmet at attachment point 1325. Elastic strap 1315 is shown in a retracted state 1320. A tight fitting head cap 1310 is worn by the user that connects the head to attachment point 1305. Contracted state 1320 has a length 1312 that may be of any variety depending on head and helmet sizes or level of impact acceleration desired.

Turning now to FIG. 14 is a side schematic view of helmet 1400 with shell 105 having elastic strap 1315 in an extended state 1316 after impact. As can readily be seen, while impact is occurring, the bladder compresses, air is expelled, and the elastic strap extends. This all occurs in microseconds after impact.

Turning now to FIG. 15 is side schematic views of a helmet 1500 with bladder and straps in a contracted and extended state according to a preferred embodiment of the invention. Bladder 1505 is bonded to the helmet on the inside of shell 105 and attached to head cap 1510. On each side of head cap 1510 are attachment points for elastic strap 1315 shown in a relaxed state having length 1312 and in extended state 1316 after impact. The elastic straps 1315 may be positioned on the back and both sides of the user's head area and arranged as shown. After impact, the elastic straps 1315 return the helmet back to a rest position, thereby re-inflating the bladders 1505 by causing the bladder 1505 to draw air through the valves and back into the bladder 1505 as the elastic straps 1315 return to their un-extended shorter state.

Turning now to FIG. 16 is flow chart 1600 of customized and optimized fit and sizing for a helmet according to a preferred embodiment of the invention. At step 1605, helmet measures are taken for a particular user, specifically at step 1610, a player's head front to back, side to side, height above eye level and circumference of the head are measured and recorded. At step 1615, the player's maximum running speed and acceleration off a line are measured and recorded. At step 1620, a calculation for size of helmet is made so that the individual player's head has sufficient travel distance in all directions of the helmet to limit head g forces to a minimum at a player's maximum helmet speed and acceleration. Step 1625 has the design for each of the 5 bladders according to the already measured player head size and shape to optimize cushioning in all directions. Step 1630 involves a custom helmet fitting for the player to permit small adjustments of the straps, attachment points, bladder location and size and head cap.

Turning now to FIG. 17 is flow chart 1700 of customized and optimized software or firmware with annual updating for a helmet according to a preferred embodiment of the invention. After a hit is experienced at step 1705, data is recorded at step 1710 for each bladder pressure and maximum pressure is compared for each bladder with an individual player template for optimum play protocol. Step 1715 logs head acceleration results and are compared with cumulative safety total, with a maximum number of allowable accelerations for a game or season. Step 1725 determines if a single threshold is exceeded, the helmet signals an alarm operably connected to the microcontroller and the player is sidelined and out of the game. Step 1730 logs cumulative accelerations and if a threshold is exceeded the helmet alarms the player and the player is taken out of the game. Step 1735 compares acceleration and pressure data with optimum play style template and the results are fed back into the player via voice instructions in the helmet to modify his style of hit and play. Finally, in step 1740, via Bluetooth®, the helmet transmits all acceleration and bladder pressure data totals to a storage device on the sidelines and player lifetime CTE log file is created and compares that with the player's CTE health status to a healthy template for any similarly situated player. A sideline referee can monitor players during the game and make decision of whether a player has incurred too many or too high an impact to continue play.

While the invention has been described in connection with a preferred embodiment, it is not intended to limit the scope of the invention to the particular form set forth, but on the contrary, it is intended to cover such alternatives, modifications, and equivalents as may be included within the spirit and scope of the invention as defined by the later issued claims. 

I claim:
 1. A smart helmet for protection of head injury in contact sports comprising: a. a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface; b. a plurality of inflatable bladders filled with air, the bladders on the interior surface of the shell; c. a valve disposed on at least one bladder responsive to signals from a controller; d. at least one flexible extendible strap having a first relaxed state and a second extended state operably engaged to at least one bladder and at least one point on the inside of the helmet; e. at least one accelerometer attached to the helmet operably connected to the helmet body for sensing g force change on the helmet in operation; f. at least a second accelerometer operably connected to the wearer's head for sensing g force change on the wearer's head in operation, g. an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met; and h. the valve, in response to control signals from a controller, exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder.
 2. The smart helmet for protection of head injury in contact sports as claimed in claim 1 wherein the accelerometer measures in the x, y and z directions.
 3. The smart helmet for protection of head injury in contact sports as claimed in claim 1 wherein the bladders are comprised of foam.
 4. The smart helmet for protection of head injury in contact sports as claimed in claim 1 further comprising a head cap connected to the inside of the helmet.
 5. The smart helmet for protection of head injury in contact sports as claimed in claim 1 further comprising a plurality of straps.
 6. The smart helmet for protection of head injury in contact sports as claimed in claim 1 wherein the valve is spring biased in a closed position.
 7. The smart helmet for protection of head injury in contact sports as claimed in claim 1 wherein the valve is operably connected to an electric motor.
 8. A smart helmet for protection of head injury in contact sports comprising: a. a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface; b. a plurality of inflatable bladders having memory foam in the bladder, the bladder positioned on the interior surface of the shell; c. a valve disposed on each bladder responsive to signals from a controller; d. a memory foam material in at least one bladder that has a resting configuration and a second compressed configuration, that re-inflates the bladder after an impact event by drawing atmospheric air through the valve and returns to the resting configuration; e. at least one accelerometer attached to the helmet operably connected to the helmet body for sensing force change on the helmet in operation; f. at least a second accelerometer attached to the helmet operably connected to the wearer's head for sensing g force change on the wearer's head in operation, g. an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met; and where the controller produces a signal and the controller: h. expels air through the valve to atmosphere in response to the signal; and i. re-inflates the bladder by drawing air into the valve as the memory foam resumes its resting shape; and closes the valve awaiting the next impact event.
 9. A smart helmet for protection of head injury in contact sports as claimed in claim 8 further comprising a head accelerometer operably engaged to the user.
 10. A smart helmet for protection of head injury in contact sports as claimed in claim 8 further comprising pressure sensors operably connected to the bladders.
 11. A smart helmet for protection of head injury in contact sports as claimed in claim 8 further comprising digital memory.
 12. A smart helmet for protection of head injury in contact sports as claimed in claim 8 further comprising an operable connection to software for analyzing player impact events.
 13. A smart helmet for protection of head injury in contact sports as claimed in claim 8 wherein the helmet is configured to a particular player's head dimensions.
 14. A smart helmet for protection of head injury in contact sports as claimed in claim 8 wherein the stored data pertaining to head impacts generates a signal to the microcontroller regarding minimum thresholds having been met.
 15. A smart helmet for protection of head injury in contact sports as claimed in claim 8 wherein the valves are spring biased in a closed position.
 16. A smart helmet for protection of head injury in contact sports as claimed in claim 8 where the bladders have a thickness dimension between approximately one to four inches.
 17. A smart helmet for protection of head injury in contact sports comprising: a. a hard shell defining a compartment for receiving a portion of a wearer's head, the shell having an interior surface and an exterior surface; b. a plurality of inflatable bladders filled with air, each bladder positioned on the interior surface of the shell; c. a valve disposed on each bladder responsive to signals from a controller; d. a memory containing material in at least one bladder that re-inflates the bladder after an impact event by drawing atmospheric air through the valve; e. a least one accelerometer attached to the helmet operably connected to the helmet body for sensing acceleration change on the helmet in operation; f. at least a second accelerometer operably connected to the wearer's head for sensing g force change on the wearer's head in operation, g. an electrically actuated valve on the bladder responsive to an accelerometer measurement determined by the controller threshold being met; and where the controller produces a signal and the controller: h. activates a motor by electrical power to one or more valves to an open state to expel air; and i. turns off electrical power to return the valves to a closed state.
 18. The smart helmet for protection of head injury in contact sports as claimed in claim 17 wherein the motor is battery powered.
 19. The smart helmet for protection of head injury in contact sports as claimed in claim 18 further comprising a transmitter of data to a remote storage device.
 20. The smart helmet for protection of head injury in contact sports as claimed in claim 17 wherein the controller thresholds are modified interactively using historical user impact event data stored in a memory. 